Method for spectral ct local tomography

ABSTRACT

A method for performing reconstruction for a region of interest (ROI) of an object is provided. The method includes designating the ROI within the object, the ROI being located within a scan field of view (FOV) of a combined third- and fourth-generation CT scanner, the CT scanner including fixed photon-counting detectors (PCDs), and an X-ray source that rotates about the object in synchronization with a rotating detector. Further, the method includes determining, for each PCD, as a function of view angle, an on/off timing schedule, based on a size and location of the designated ROI, and performing a scan to obtain a first data set from the rotating detector and a second data set from the plurality of PCDs, while turning each PCD on and off according to the determined schedule. Finally, the method includes performing reconstruction using the first and second data sets to obtain ROI spectral images.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional application of U.S. application Ser.No. 14/063,008, filed Oct. 25, 2013, the entire contents of which areincorporated herein by reference.

FIELD

Embodiments disclosed herein generally relate to methods for computedtomography (CT) imaging. In particular, embodiments disclosed hereinrelate to an apparatus and an associated method for spectral CTreconstruction for one or more regions of interest.

BACKGROUND

Radiographic imaging, in its simplest expression, is an X-ray beamtraversing an object and a detector relating the overall attenuation perray. The attenuation is derived from a comparison of the same ray withand without the presence of the object. From this conceptual definition,several aspects are required to properly construct an image in 3D. Forinstance, the finite size of the X-ray focal spot, the nature and shapeof the filter blocking the very low-energy X-ray from the tube, thedetails of the geometry and characteristics of the detector and thecapacity of the data acquisition system are all elements that affect howthe actual reconstruction is performed.

CdTe/CZT-based photon-counting detectors suffer from polarization uponirradiation by non- or low-attenuated beams near the edges of the scanfield of view (FOV) and/or after scanning low-attenuation regions of thepatient, e.g., the lung. Dynamic (mechanical) bowtie filters orcollimators that attempt to attenuate such beams to compensate for thevariations in patient size and shape is not feasible due to fast CTgantry rotation speeds, high centrifugal forces on the gantry rotatingbase, and system reliability challenges.

BRIEF DESCRIPTION OF THE DRAWINGS

A more complete appreciation of the disclosed embodiments and many ofthe attendant advantages thereof will be readily obtained as the samebecomes better understood by reference to the following detaileddescription when considered in connection with the accompanyingdrawings, wherein:

FIG. 1 illustrates a combined third-fourth-generation CT scanneraccording to one embodiment;

FIG. 2 illustrates designation of one or more regions of interest (ROIs)within an object;

FIGS. 3 and 4 illustrates a combined third-fourth-generation CT scannerin which PCDs are turned on and off based on the size and location ofthe ROIs.;

FIG. 5 illustrates a method for determining whether a given PCD shouldbe on or off based on a given ROI and X-ray source position, accordingto one embodiment;

FIG. 6 illustrates slow kVp switching according to one embodiment;

FIGS. 7 and 8 illustrate the switching between two bowtie filtersaccording to one embodiment;

FIG. 9 illustrates a dual-source, dual-detector scanner;

FIG. 10 illustrates a CT scanner according to one embodiment;

FIG. 11 illustrates a method of performing spectral reconstruction of anROI with a combined third- and fourth-generation CT scanner;

FIG. 12 illustrates a method of performing spectral reconstruction of anROI using slow kVp switching; and

FIG. 13 illustrates a method of performing spectral reconstruction of anROI using a dual-source, dual-energy CT scanner.

DETAILED DESCRIPTION

Embodiments disclosed herein relate to methods for performing spectralreconstruction of a region of interest of an object using various CTscanner architectures.

In particular, in one embodiment, there is provided a method ofperforming spectral reconstruction for a region of interest (ROI) of anobject, the method comprising: (1) designating the ROI within theobject, the ROI being located within a scan field of view (FOV) of acombined third- and fourth-generation computed tomography (CT) scanner,the CT scanner including a plurality of fixed photon-counting detectors(PCDs), and an X-ray source that rotates in a trajectory about theobject in synchronization with an energy-integrating detector; (2)determining, for each PCD of the plurality of PCDs, as a function of aposition of the X-ray source along the trajectory, an on/off timingschedule of the PCD, based on a size and location of the designated ROI,(3) performing a scan of the object by rotating the X-ray source and theenergy-integrating detector to obtain a first data set from theenergy-integrating detector and a second data set from the plurality ofPCDs, wherein the step of performing the scan includes turning each PCDon and off according to the determined on/off timing schedule of thePCD; and (4) performing spectral reconstruction within the ROI using thefirst and second data sets to obtain spectral images of the ROI.

In one embodiment, the step of performing reconstruction furthercomprises generating a full energy-integrating image within the scanFOV.

In another embodiment, the step of performing the scan comprises turningeach PCD on and off by controlling a bias voltage of the PCD.

In another embodiment, the designating step comprises: (1) obtaining ascout scan of the object; and (2) receiving designation of the ROI froma user input device, based on the scout scan.

In another embodiment, there is provided an apparatus for performingspectral reconstruction for a region of interest (ROI) of an object, theapparatus being communicatively connected to a combined third- andfourth-generation computed tomography (CT) scanner, the CT scannerincluding a plurality of fixed photon-counting detectors (PCDs), and anX-ray source that rotates in a trajectory about the object insynchronization with an energy-integrating detector, the apparatuscomprising a circuit configured to (1) receive designation of the ROIwithin the object, the ROI being located within a scan field of view(FOV) of the CT scanner; (2) determine, for each PCD of the plurality ofPCDs, as a function of a position of the X-ray source along thetrajectory, an on/off timing schedule of the PCD, based on a size andlocation of the designated ROI; (3) cause the CT scanner to perform ascan of the object by rotating the X-ray source and theenergy-integrating detector to obtain a first data set from theenergy-integrating detector and a second data set from the plurality ofPCDs, wherein circuit is further configured to send signals to the CTscanner to turn each PCD on and off according to the determined on/offtiming schedule of the PCD; and (4) perform spectral reconstructionwithin the ROI using the first and second data sets to obtain spectralimages of the ROI.

In another embodiment, there is provided a CT scanner for performingspectral reconstruction for a region of interest (ROI) of an object, theapparatus comprising: (1) a combined third- and fourth-generationcomputed tomography (CT) scanner, the CT scanner including a pluralityof fixed photon-counting detectors (PCDs), and an X-ray source thatrotates in a trajectory about the object in synchronization with anenergy-integrating detector; and 92) a circuit configured to (a) receivedesignation of the ROI within the object, the ROI being located within ascan field of view (FOV) of the CT scanner; (b) determine, for each PCDof the plurality of PCDs, as a function of a position of the X-raysource along the trajectory, an on/off timing schedule of the PCD, basedon a size and location of the designated ROI; (c) cause the CT scannerto perform a scan of the object by rotating the X-ray source and theenergy-integrating detector to obtain a first data set from theenergy-integrating detector and a second data set from the plurality ofPCDs, wherein circuit is further configured to send signals to the CTscanner to turn each PCD on and off according to the determined on/offtiming schedule of the PCD; and (d) perform spectral reconstructionwithin the ROI using the first and second data sets to obtain spectralimages of the ROI.

In another embodiment, there is provided a method of performing spectralreconstruction for a region of interest (ROI) of an object, the methodcomprising: (1) designating the ROI within the object, the ROI beinglocated within a scan field of view (FOV) of a computed tomography (CT)scanner having an X-ray source; (2) performing a first scan of theobject using a first peak voltage of the X-ray source and a firstfilter, to obtain a first data set, the first filter corresponding tothe scan FOV; (3) performing a second scan of the object using a secondpeak voltage of the X-ray source and a second filter, to obtain a seconddata set, the second filter resulting in a FOV corresponding to the ROI;and (4) performing spectral reconstruction within the ROI using thefirst and second data sets to obtain spectral images of the ROI.

In another embodiment, the method included switching from the firstfilter to the second filter after the first scan but before the secondscan, wherein the first and second filters are bowtie filters.

In another embodiment, there is provided an apparatus for performingspectral reconstruction for a region of interest (ROI) of an object, theapparatus being communicatively connected to a computed tomography (CT)scanner having an X-ray source, the apparatus comprising a circuitconfigured to (1) receive designation of the ROI within the object, theROI being located within a scan field of view (FOV) of the computedtomography (CT) scanner; (2) cause the CT scanner to perform a firstscan of the object using a first peak voltage of the X-ray source and afirst filter, to obtain a first data set, the first filter correspondingto the scan FOV; (3) cause the CT scanner to perform a second scan ofthe object using a second peak voltage of the X-ray source and a secondfilter, to obtain a second data set, the second filter resulting in aFOV corresponding to the ROI; and (4) perform spectral reconstructionwithin the ROI using the first and second data sets to obtain spectralimages of the ROI.

In another embodiment, there is provided a method of performing spectralreconstruction for a region of interest (ROI) of an object, the methodcomprising: (1) designating the ROI within the object, the ROI beinglocated within a scan field of view (FOV) of a dual-source, dualdetector computed tomography (CT) scanner, the CT scanner having a firstX-ray source and a second X-ray source; (2) setting a first peak voltageand a first FOV for the first X-ray source; (3) setting a second peakvoltage and a second FOV for the second X-ray source, the second FOVcorresponding to the ROI; (4) performing a scan of the object using thefirst and second X-ray sources to obtain first and second data sets,respectively; and (5) performing spectral reconstruction within the ROIusing the first and second data sets to obtain spectral images of theROI.

In one embodiment, the CT scanner includes a first detector and a seconddetector, and the first and second detectors have different sizes.

In another embodiment, there is provided an apparatus for performingspectral reconstruction for a region of interest (ROI) of an object, theapparatus being communicatively connected to a dual-source, dualdetector computed tomography (CT) scanner, the CT scanner having a firstX-ray source and a second X-ray source, the apparatus comprising acircuit configured to (1) receive designation of the ROI within theobject, the ROI being located within a scan field of view (FOV) of thedual-source, dual detector CT scanner; (2) set a first peak voltage anda first FOV for the first X-ray source; (3) set a second peak voltageand a second FOV for the second X-ray source, the second FOVcorresponding to the ROI; (4) cause the CT scanner to perform a scan ofthe object using the first and second X-ray sources to obtain first andsecond data sets, respectively; and (5) perform spectral reconstructionwithin the ROI using the first and second data sets to obtain spectralimages of the ROI.

3^(rd)/4^(th) Generation Architecture

FIG. 1 illustrates a combined third and spectral fourth-generation CTscanner, which includes an X-ray tube and a first detector that rotatetogether, along with a second, stationary detector formed of sparse,photon-counting detector (PCD) elements. In one embodiment, the firstdetector includes conventional energy-integrating (EI) detectorelements.

As shown in FIGS. 1 and 2, within the spectral region of interest (ROI),a user can prescribe one or more smaller ROIs, having various sizes andaspect ratios, for spectral imaging, based on scout scans. Theuser-prescribed ROIs are within the regions of the patient where theX-ray beam is attenuated by a bowtie filter and the patient body tolevels that are appropriate for PCDs. In addition, the location, shape,and size of a user-prescribed ROI can vary in the z-direction for volumeaxial or helical scans.

Prior to the scan, based on the location of the user-prescribed ROI(s)and various scan parameters, a system controller calculates an ON/OFFtiming schedule to be used during the scan for each of the sparse fourthgeneration PCDs. During the scan, energy-integrating data is collectedby the first detector for the full FOV with the third-generation system.In addition, truncated spectral data (for the user-prescribed ROIs only)is collected by the sparse fourth-generation PCDs. Note that, during thescan, the system controller turns each PCD ON and OFF with therespective bias voltage, based on the predetermined ON/OFF timingschedule.

FIGS. 3 and 4 illustrate examples of the fixed, sparse PCDs being turnedON and OFF as the X-ray source rotates, based on the size and locationof the one or more user-prescribed ROIs. Note that, as shown in FIGS. 4and 5, a given PCD can be OFF or ON depending on the location of theX-ray source during the scan.

FIG. 5 is a diagram for explaining how the system controller determineswhen to turn each PCD ON or OFF during the scan based on the scannergeometry and the location of a user-prescribed ROI. The “PCD ON” periodfor a PCD and a given ROI can be described in terms of the X-ray tubeposition, i.e., view number.

In this example, the illustrated PCD is fixed at a distance D from theisocenter, at angular position α relative to the CT gantry. Further, theillustrated ROI is round and has a radius of r₀ and a center at adistance R₀ from the isocenter, with a center angular position of Φ₀(relative to the CT gantry). Thus, for an X-ray tube with focal spotrotating around the isocenter at a radius L, the angular range (view #s)of the tube corresponding to the ROI for the given PCD can be calculatedas follows (in terms of θ₁ and Θ₂):

$k = \sqrt{R_{0}^{2} + D^{2} - {2R_{0}D\; {\cos \left( {\alpha - \varnothing_{0}} \right)}}}$$\delta = {\sin^{- 1}\frac{r_{0}}{k}}$$\beta = {\cos^{- 1}\frac{D^{2} + k^{2} - R_{0}^{2}}{2{Dk}}}$$k_{1} = {{D\; {\cos \left( {\beta - \delta} \right)}} + \sqrt{L^{2} - {D^{2}{\sin^{2}\left( {\beta - \delta} \right)}}}}$$k_{2} = {{D\; {\cos \left( {\beta + \delta} \right)}} + \sqrt{L^{2} - {D^{2}{\sin^{2}\left( {\beta + \delta} \right)}}}}$$\theta_{1} = {\alpha - {\cos^{- 1}\frac{k_{1}^{2} - L^{2} - D^{2}}{2{DL}}}}$$\theta_{2} = {\alpha - {\cos^{- 1}\frac{k_{2}^{2} - L^{2} - D^{2}}{2{DL}}}}$

The angles θ₁ and θ₂ determine the view numbers for the PCD ON state forthe given PCD. The calculation for each of the other PCDs is similar.

After the scan, the full-view energy-integrating data and the truncatedspectral data are used for reconstruction within the user-prescribedROIs. An example of such a reconstruction algorithm is the compressivesensing-based statistical interior tomography method (CS-SIT). Thereconstruction process generates both the full EI image within the scanFOV and spectral images within the user-prescribed ROIs, which aredisplayed to the user.

Note that an advantage of this embodiment is that ROIs can be easilydefined so that a variable portion of the object can be imaged, whileprotecting the PCD detector elements from the high flux of anunobstructed beam.

FIG. 11 shows a flowchart that describes a method according to oneembodiment.

In particular, in step 1110, the operator designates one or more ROIswith the scan FOV, based, e.g., from viewing a scout scan.

In step 1120, a processor or specialized circuit determines, for eachPCD, an on/off timing schedule based on size and location of the ROIs,using the process described above.

In step 1130, a scan is performed by rotating the X-ray source and theenergy-integrating detector to obtain a first data set from theenergy-integrating detector and a second data set from the plurality ofPCDs, while turning each PCD on and off according to the determinedon/off timing schedule of the PCD.

In step 1140, spectral reconstruction is performed within the ROI usingthe first and second data sets to obtain spectral images of the ROI.

In step 1150, the spectral images and a full EI image are displayed.

Slow-KVP Switching

In another embodiment, slow kVp (peak kilovoltage) switching is used toobtain two data sets for truncated reconstruction of one or moreuser-prescribed ROIs. Note that any type of scanner architecture and anytype of detector elements can be used in this embodiment.

In particular, as shown in FIGS. 6-8, two bowtie filters are used toobtain two different scan FOVs. In the first scan, the large-FOV bowtiefilter is used together with a first kVp₁ (a high kVp) to obtain a firstdata set.

Then, as shown in FIG. 8, the bowtie filter is switched after the firstscan to obtain a smaller-FOV filter by moving the filter in the zdirection. Note that the range of movement in the z direction dependsupon the desired z coverage. Note also that half scans (plus DET fanangle) from behind the table can also be used to further reduce theradiation dose.

In another embodiment, the bowtie switching can be implemented byinserting an additional attenuation block onto the existing large-FOVbowtie filter to obtain the smaller-FOV bowtie filter.

Next, as shown in FIGS. 6 and 8, a second scan with the smaller-FOVbowtie filter and a second, different kVp₂ (a low kVp) is performed toobtain a second data set.

Next, the first data set corresponding to the large-FOV/kVp₁ scan andthe second data set corresponding to the smaller-FOV/kVp₂ scan are usedin a reconstruction process. In particular, the reconstruction processgenerates a full EI image for the large FOV and spectral images for thesmaller FOV, which are displayed to the user. An advantage of thisembodiment is that spectral images are obtained at a lower radiationdose.

FIG. 12 shows a flowchart that describes a method according to oneembodiment.

In particular, in step 1210, the operator designates one or more ROIswith the scan FOV, based, e.g., from viewing a scout scan.

In step 1220, a first scan of the object is performed using a first peakvoltage of the X-ray source and a first filter, to obtain a first dataset, the first filter corresponding to the scan FOV.

In step 1230, a second scan of the object is performed using a secondpeak voltage of the X-ray source and a second filter, to obtain a seconddata set, the second filter resulting in a FOV corresponding to the ROI.

In step 1240, spectral reconstruction is performed within the ROI usingthe first and second data sets to obtain spectral images of the ROI.

In step 1250, the spectral images and a full EI image are displayed.

Dual-Source/Dual-Detector

In another embodiment, a dual-source, dual-detector scanner is used toobtain two data sets for truncated reconstruction of one or moreuser-prescribed ROIs. In this embodiment, as shown in FIG. 9, adifferent scan FOV and/or different detector sizes are used for thedifferent source/detector pairs, based on the user-prescribed ROI(s).Further, a different kVp is used for the two sources during the scan,similar to the slow kVp switching embodiments, to obtain first andsecond data sets, respectively. For example, the first source/detectorpair has a large FOV and uses kVp₁, while the second source/detectorpair has a smaller FOV and uses kVp₂. In one embodiment, both detectorsuse EI detector elements.

Next, the first data set corresponding to the large-FOV/kVp₁ scan andthe second data set corresponding to the smaller-FOV/kVp₂ scan are usedin a reconstruction process. In particular, the reconstruction processgenerates a full EI image for the large FOV and spectral images for thesmaller FOV, which are displayed to the user. An advantage of thisembodiment is that spectral images are obtained at a lower radiationdose.

In an alternative embodiment, one of the detectors, or the centerportion of the detectors, can be spectral detectors (e.g., photoncounting, dual layer), while the rest of the detector elements can beenergy-integrating detector elements. This also allows different FOVsfor different detectors for dose considerations. When CdTe/CZT-basedphoton-counting detectors are used to collect spectral data for thesmaller FOV/ROI, detector polarization is mitigated.

FIG. 13 shows a flowchart that describes a method according to oneembodiment.

In particular, in step 1310, the operator designates one or more ROIswith the scan FOV, based, e.g., from viewing a scout scan.

In step 1320, a first peak voltage and a first FOV for the first X-raysource is set and a second peak voltage and a second FOV for the secondX-ray source is set, the second FOV corresponding to the ROI.

In step 1330, a scan of the object is performed using the first andsecond X-ray sources to obtain first and second data sets, respectively.

In step 1340, spectral reconstruction is performed within the ROI usingthe first and second data sets to obtain spectral images of the ROI.

In step 1350, the spectral images and a full EI image are displayed.

FIG. 10 illustrates the basic structure of a conventionalthird-generation CT apparatus that can be used in some of theembodiments disclosed herein. Note that similar hardware can be used inconjunction with the combined third- and fourth generation CT scannershown in FIG. 1, as well as dual source, dual detector CT scannersdescribed above. For example, a ring of fixed PCDs, as shown in FIG. 1,can be used in conjunction with (e.g., controlled by) the hardware shownin FIG. 10.

The CT apparatus of FIG. 10 includes an X-ray tube 1, filters andcollimators 2, and a detector 3. The X-ray source and the detector canrotate in synchronization with one another. The CT apparatus will alsoinclude additional mechanical and electrical components such as a gantrymotor and a scanner controller 4 to control the rotation of the gantry,control the X-ray source, and control a patient bed. The CT apparatusalso includes a data acquisition system 6 to obtain projection data fromthe detector 3 and a circuit 7 to generate CT images based on theprojection data acquired by the data acquisition system. As discussed inmore detail below, the circuit 7 can be a dedicated, specialize circuitor a computer (hardware) processor, such as a microprocessor, that isconfigured (e.g., programmed with computer program instructions) toperform the functions disclosed above and shown in the flowcharts. Thecircuit 7 and the data acquisition system 6 make use of a memory 8,which is configured to store, e.g., data obtained from the detector aswell as reconstructed images.

Further, the CT apparatus can include an input device 5 for receivinguser input (e.g., designating a ROI), and a display 9 to displayreconstructed spectral images, e.g., spectral images of the ROT.

The circuit 7 can be a hardware processor that executes software tocontrol the scanner controller to perform a scan and to turn PCDs on anoff according to a schedule determined by the circuit 7, as discussedabove.

As one of ordinary skill in the art would recognize, the circuit 7 caninclude a CPU that can be implemented as discrete logic gates, as anApplication Specific Integrated Circuit (ASIC), a Field ProgrammableGate Array (FPGA) or other Complex Programmable Logic Device (CPLD). AnFPGA or CPLD implementation may be coded in VHDL, Verilog, or any otherhardware description language and the code may be stored in anelectronic memory directly within the FPGA or CPLD, or as a separateelectronic memory. Further, the memory may be non-volatile, such as ROM,EPROM, EEPROM or FLASH memory. The memory can also be volatile, such asstatic or dynamic RAM, and a processor, such as a microcontroller ormicroprocessor, may be provided to manage the electronic memory as wellas the interaction between the FPGA or CPLD and the memory.

Alternatively, the CPU in the circuit 7 may execute a computer programincluding a set of computer-readable instructions that perform thefunctions described herein, the program being stored in any of theabove-described non-transitory electronic memories and/or a hard diskdrive, CD, DVD, FLASH drive or any other known storage media. Further,the computer-readable instructions may be provided as a utilityapplication, background daemon, or component of an operating system, orcombination thereof, executing in conjunction with a processor, such asa Xenon processor from Intel of America or an Opteron processor from AMDof America and an operating system, such as Microsoft VISTA, UNIX,Solaris, LINUX, Apple, MAC-OS and other operating systems known to thoseskilled in the art.

The images generated by the circuit 7 via a reconstruction process arestored in the memory 8, and/or displayed on the display 9. As one ofordinary skill in the art would recognize, the memory 8 can be a harddisk drive, CD-ROM drive, DVD drive, FLASH drive, RAM, ROM or any otherelectronic storage known in the art. The display 9 can be implemented asan LCD display, CRT display, plasma display, OLED, LED or any otherdisplay known in the art. As such, the descriptions of the memory andthe display provided herein are merely exemplary and in no way limit thescope of the present advancements.

While certain embodiments have been described, these embodiments havebeen presented by way of example only, and are not intended to limit thescope of the inventions. Indeed the novel methods and systems describedherein may be embodied in a variety of other forms; furthermore, variousomissions, substitutions, and changes in the form of the methods andsystems described herein may be made without departing from the spiritof the inventions. The accompanying claims and their equivalents areintended to cover such forms or modifications as would fall within thescope and spirit of the inventions.

1. A method of performing spectral reconstruction for a region ofinterest (ROI) of an object, the method comprising: designating the ROIwithin the object, the ROI being located within a scan field of view(FOV) of a computed tomography (CT) scanner having an X-ray source;performing a first scan of the object using a first peak voltage of theX-ray source and a first filter, to obtain a first data set, the firstfilter corresponding to the scan FOV; performing a second scan of theobject using a second peak voltage of the X-ray source and a secondfilter, to obtain a second data set, the second filter resulting in aFOV corresponding to the ROI; and performing spectral reconstructionwithin the ROI using the first and second data sets to obtain spectralimages of the ROI.
 2. The method of claim 1, wherein the step ofperforming reconstruction further comprises generating a fullenergy-integrating image within the scan FOV.
 3. The method of claim 1,further comprising displaying the spectral images of the ROI.
 4. Themethod of claim 1, further comprising switching from the first filter tothe second filter after the first scan but before the second scan. 5.The method of claim 1, wherein the first and second filters are bowtiefilters.
 6. An apparatus for performing spectral reconstruction for aregion of interest (ROI) of an object, the apparatus beingcommunicatively connected to a computed tomography (CT) scanner havingan X-ray source, the apparatus comprising: a circuit configured toreceive designation of the ROI within the object, the ROI being locatedwithin a scan field of view (FOV) of the computed tomography (CT)scanner; cause the CT scanner to perform a first scan of the objectusing a first peak voltage of the X-ray source and a first filter, toobtain a first data set, the first filter corresponding to the scan FOV;cause the CT scanner to perform a second scan of the object using asecond peak voltage of the X-ray source and a second filter, to obtain asecond data set, the second filter resulting in a FOV corresponding tothe ROI; and perform spectral reconstruction within the ROI using thefirst and second data sets to obtain spectral images of the ROI.
 7. Amethod of performing spectral reconstruction for a region of interest(ROI) of an object, the method comprising: designating the ROI withinthe object, the ROI being located within a scan field of view (FOV) of adual-source, dual detector computed tomography (CT) scanner, the CTscanner having a first X-ray source and a second X-ray source; setting afirst peak voltage and a first FOV for the first X-ray source; setting asecond peak voltage and a second FOV for the second X-ray source, thesecond FOV corresponding to the ROI; performing a scan of the objectusing the first and second X-ray sources to obtain first and second datasets, respectively; and performing spectral reconstruction within theROI using the first and second data sets to obtain spectral images ofthe ROI.
 8. The method of claim 7, wherein the step of performingreconstruction further comprises generating a full energy-integratingimage within the scan FOV.
 9. The method of claim 7, further comprisingdisplaying the spectral images of the ROI.
 10. The method of claim 7,wherein the CT scanner includes a first detector and a second detector,and the first and second detectors have different sizes.
 11. Anapparatus for performing spectral reconstruction for a region ofinterest (ROI) of an object, the apparatus being communicativelyconnected to a dual-source, dual detector computed tomography (CT)scanner, the CT scanner having a first X-ray source and a second X-raysource, the apparatus comprising: a circuit configured to receivedesignation of the ROI within the object, the ROI being located within ascan field of view (FOV) of the dual-source, dual detector CT scanner;set a first peak voltage and a first FOV for the first X-ray source; seta second peak voltage and a second FOV for the second X-ray source, thesecond FOV corresponding to the ROI; cause the CT scanner to perform ascan of the object using the first and second X-ray sources to obtainfirst and second data sets, respectively; and perform spectralreconstruction within the ROI using the first and second data sets toobtain spectral images of the ROI.